Muscle fatigue detection and treatment integrated fabric electronic system

Abstract

The invention discloses a muscle fatigue detection and treatment integrated fabric electronic system, which is characterized in that conductive fabric lines, physiological electrodes, vertical interconnected via holes and patch-type components are integrated on the same fabric substrate, and the conductive fabric lines are arranged on the surfaces of the two sides of the fabric substrate and are communicated with each other through the vertical interconnected via holes; the integrally formed circuit comprises an electrode array and a signal conditioning circuit, the electrode array is used for detecting electromyographic signals and applying transcutaneous electrical stimulation, and the signal conditioning circuit is used for electromyographic signal amplification, electrical stimulation waveform conditioning and overall sequential logic control and has the functions of safety isolation and electrical stimulation waveform detection. Components can be highly integrated on a single piece of fabric through process design, and electromyographic signal acquisition and transcutaneous electrical stimulation are realized. Experiments prove that when the system is worn on the arm, the fatigue process of the biceps brachii muscle can be monitored, fatigue recovery is effectively promoted, and the capacity of the system in closed-loop diagnosis and treatment is shown.

Description

Technical Field

[0001] The invention belongs to the technical field of intelligent electronic fabrics and relates to a fabric electronic system integrating muscle fatigue detection and treatment. Background Art

[0002] Textiles with electronic components offer a portable and personalized approach to health monitoring and treatment. However, existing solutions often fail to integrate hierarchical circuits and high-density chips on or inside textiles, and usually rely on external commercial circuit boards, which hinders system-level portability and wearable comfort.

[0003] We use laser integrated manufacturing technology to achieve close integration of double-layer circuits, electrodes and flexible sensors on a single piece of fabric, which helps to realize a wireless, wearable, breathable health electronic system. Based on this, the present invention further designs a wireless, monolithic integrated, breathable and wearable textile electronic system to meet the needs of integrated detection and treatment for precision medicine, which can simultaneously realize the functions of monitoring and relieving muscle fatigue. The overall area of ​​the circuit in this textile electronic system can be less than 50cm 2 , can be worn on parts of the human body such as the biceps, quadriceps, etc. to play a role.

[0004] Compared with the existing technology, the present invention can realize signal processing and wireless transmission without the need for an external commercial circuit board, and has good breathability and wearing comfort. It can not only detect physiological signals, but also apply transcutaneous electrical stimulation therapy to muscles to relieve muscle fatigue, thus realizing the integration of detection and treatment. Summary of the invention

[0005] The purpose of the present invention is to address the deficiencies of the prior art and provide a textile electronic system that integrates muscle fatigue detection and treatment. The textile electronic system integrates functional fabrics, flexible electronic components, rigid electronic components, conductive fabric threads and physiological electrodes on both sides of a single piece of fabric, and can integrate monitoring and treatment, and has great potential in closed-loop diagnosis and treatment.

[0006] The technical solution adopted by the present invention is:

[0007] A fabric electronic system integrating muscle fatigue detection and treatment is a fabric substrate on which conductive fabric lines and physiological electrodes, vertical interconnection vias and patch components are integrated. Conductive fabric lines are provided on both side surfaces of the fabric substrate and are interconnected through vertical interconnection vias. The overall circuit includes an electrode array and a signal conditioning circuit, wherein the electrode array is used to detect electromyographic signals and to apply transcutaneous electrical stimulation, and the signal conditioning circuit is used for electromyographic signal amplification, electrical stimulation waveform conditioning and overall timing logic control, and has the functions of safety isolation and electrical stimulation waveform detection.

[0008] In the above technical scheme, further, a single pair of electrodes is multiplexed to construct the electrode array, and the electrode array includes electrodes 1 to 4, wherein electrode 1 and electrode 2 are the positive and negative input terminals of the electromyographic signal, electrode 3 is the positive output terminal of the electrical stimulation, and electrode 4 serves as both the negative output terminal of the electrical stimulation and the output terminal of the right leg drive circuit; wherein the electrode used for signal sampling is separated from the electrode used for applying electrical stimulation to avoid the signal sampling being affected by electrode polarization.

[0009] Furthermore, the signal conditioning circuit uses three independent optocouplers and an H-bridge circuit composed of four optocouplers, wherein electrode No. 1, electrode No. 2, and electrode No. 4 are respectively connected to the peripheral circuit through an independent optocoupler, and electrode No. 3 and electrode No. 4 are connected to the peripheral circuit through the H-bridge circuit. The four electrodes are selectively connected to the circuit by controlling the optocouplers to achieve switching between electromyography detection and electrical stimulation modes.

[0010] Furthermore, a constant current source is used in the signal conditioning circuit to output the stimulation current, the amplitude of the stimulation current is controlled by the digital-to-analog converter of the microcontroller, the direction of the stimulation current is controlled by the H-bridge circuit at the load end of the constant current source, and the duty cycle, frequency, and amplitude of the stimulation current are all adjustable in real time to ensure the output of electrically neutral current.

[0011] Furthermore, in the electrical stimulation mode, the independent optocouplers connected to electrodes 1, 2, and 4 are blocked, and the optocouplers in the H-bridge circuit are switched in an orderly manner; in the electromyography detection mode, the optocouplers in the H-bridge circuit are blocked, and the independent optocouplers connected to electrodes 1, 2, and 4 are normally open.

[0012] Furthermore, the vertical interconnected vias are locations on the fabric substrate where vias need to be formed to connect the circuits on both sides of the fabric. The conductive slurry is infiltrated into the texture structure of the fabric substrate at that location using air pressure injection, so that the corresponding area of ​​the fabric substrate is connected on the front and back sides.

[0013] Furthermore, the conductive fabric wires and physiological electrodes are formed by cutting the conductive fabric according to a pre-designed pattern using a laser, and then transferring the conductive fabric wires and physiological electrodes to both sides of the fabric substrate using a transfer method. The conductive fabric wires and physiological electrodes on both sides are connected through the vertical interconnecting vias.

[0014] Furthermore, the surface mount components are soldered onto the conductive fabric line using solder paste to form a complete circuit.

[0015] Furthermore, on the lower surface of the fabric base are sequentially conductive fabric lines and a physiological electrode layer, as well as a medical double-sided adhesive tape and a hydrogel layer; the medical double-sided adhesive tape and the hydrogel layer are formed by laser cutting of the medical double-sided adhesive tape into grooves of the same shape as the physiological electrodes, and a hydrogel precursor liquid is injected into the grooves and cured by ultraviolet light; on the upper surface of the fabric base are distributed conductive fabric lines and patch electronic devices.

[0016] The present invention has the following beneficial effects:

[0017] 1. The scheme of the present invention realizes the integrated integration of rigid electronic devices such as patch electronic components, flexible electronic devices such as physiological electrodes, inner and outer double-layer conductive fabric lines, and vertical interconnection vias on the same fabric. Moreover, since a double-layer conductive circuit with independent wiring is realized on a single piece of fabric, a circuit layout with a higher degree of integration can be allowed compared with the prior art; and at the same time, it can ensure that the corresponding fabric electronic system has the characteristics of breathability, wearability, and treatment safety.

[0018] 2. The solution of the present invention can simultaneously realize the functions of monitoring and relieving muscle fatigue without the need for an external commercial circuit board, and is used for integrated detection and treatment of muscle fatigue. BRIEF DESCRIPTION OF THE DRAWINGS

[0019] Figure 1 It is a geometric structure diagram and a cross-sectional diagram of the electrode array of the textile electronic system of the present invention.

[0020] Figure 2 It is a schematic diagram of the working mode of the electrode array of the textile electronic system of the present invention.

[0021] Figure 3 It is a 3D exploded view of the textile electronic system of the present invention.

[0022] Figure 4 The figures are the actual picture and wearing effect picture of the textile electronic system of the present invention.

[0023] Figure 5 It is a program logic diagram of the fabric electronic system of the present invention in two modes: electromyographic detection / electrical stimulation application.

[0024] Figure 6 It is a functional block diagram of the textile electronic system of the present invention.

[0025] Figure 7 The current (Figure a) and voltage (Figure b) generated by the fabric electronic system of the present invention when transcutaneous electrical stimulation is applied to the biceps brachii, as well as the electromyographic signal (Figure c) and its power spectrum density (Figure d) generated when the biceps brachii contracts.

[0026] Figure 8The current consumption of the textile electronic system of the present invention and a commercial PCB with the same function in different modes is compared (Figure a), and the waveforms of applied electrical stimulation are compared (Figures b and c).

[0027] Fig. 9 When a load of 5 kg is applied to the biceps brachii, the electromyographic signal (Fig. a) and its root mean square (Fig. b) and short-time Fourier transform spectrum (Fig. c) collected by the textile electronic system of the present invention are shown.

[0028] Fig.10 It is the median frequency (MDF) of the electromyographic signal of the textile electronic system of the present invention during biceps fatigue and after resting for 10 seconds, and the statistical interval is 5 to 160 Hz.

[0029] Fig.11 This is the relationship between the maximum voluntary contraction force (MVC) and time during the fatigue recovery process of the biceps brachii. Specific implementation methods

[0031] The textile electronic system of the present invention is further described below with reference to the accompanying drawings and embodiments.

[0032] A fabric electronic system for integrated muscle fatigue detection and treatment of the present invention is formed on the same fabric substrate based on laser integrated manufacturing process, pneumatic perfusion process, transfer method combined with welding and other processes, and integrated with conductive fabric wires and physiological electrodes, vertical interconnection vias and patch components. Conductive fabric wires are provided on both sides of the fabric substrate and are connected to each other through vertical interconnection vias, that is, a double-layer circuit structure is formed on a single-layer fabric; the overall circuit includes an electrode array and a signal conditioning circuit. According to a specific embodiment of the present invention, the circuit also has a wireless transmission module, and the system also includes a host computer; wherein the electrode array is used to detect electromyographic signals, and the median frequency of the electromyographic signals is used to evaluate the degree of muscle fatigue. At the same time, the physiological electrodes are used to apply transcutaneous electrical stimulation therapy, so that the maximum autonomous contraction force of the muscles is restored faster. The signal conditioning circuit fully considers the constraints of the fabric electronic manufacturing process and the miniaturization requirements of wearable devices, and is used for electromyographic signal amplification, electrical stimulation waveform conditioning and overall sequential logic control, and has the functions of safety isolation and electrical stimulation waveform detection.

[0033] The specific circuit in the textile electronic system of the present invention can be designed accordingly according to the functions to be realized. The textile substrate in the textile electronic system is one or more of modal knitted fabric, medical nonwoven fabric, polyimide PI fabric or polyester taffeta fabric, etc. The vertical interconnection vias are formed at the positions where vias are required to connect the circuits on both sides of the textile substrate according to the design drawings. Specifically, the air pressure perfusion method is adopted to brush the conductive slurry on both sides of the required position, and the conductive slurry is infiltrated into the texture structure of the textile substrate at the position by blowing air through an air gun on both sides, so that the corresponding area of ​​the textile substrate is connected to the front and back sides. The conductive slurry used is preferably an intermetallic compound LM / Cu NP slurry formed by mixing liquid metal and copper nanoparticles by a centrifugal mixer or a high-speed defoaming machine. The tangential force generated during the centrifugation process is used to destroy the oxide film on the surface of LM, so that LM and Cu NP fully react during the mixing process, and no additional chemical reagents such as acid and alkali are introduced. The mixing is uniform and the effect is excellent. The conductive fabric line and physiological electrode are formed by cutting the conductive fabric according to a pre-designed pattern using a laser, and then transferring the conductive fabric line and physiological electrode to both sides of the fabric substrate using a transfer method, and the conductive fabric line and physiological electrode on both sides are connected through the vertical interconnection vias. Specifically, the following method can be used: a layer of adhesive film (AL) is pressed on one side of a metal fabric (MT), and a layer of adhesive water-soluble sacrificial layer (SL) is pressed on the other side of the metal fabric to form an AL / MT / SL structure, and a patterned conductive circuit is cut from the AL and MT layers using an ultraviolet nanosecond laser, while the SL remains intact, and the entire AL / MT / SL is attached to the fabric substrate with the AL surface, and then immersed in water, and the SL layer is removed after softening in the water, and the AL / MT layer attached to the fabric substrate is dried, and the excess AL / MT layer except the patterned conductive circuit is peeled off to form a conductive fabric line or physiological electrode. The surface-mount components are soldered to the conductive fabric line using solder paste to form a complete circuit, wherein the solder paste is preferably a low-melting-point solder paste formed by mixing tin paste and aluminum flux to effectively remove the nickel oxide layer of commercial surface-mount electronic components to ensure the welding effect.

[0034] like Figure 1-11 FIG. 1 is a specific embodiment of the present invention, in which:

[0035] (1) An electrode array was constructed by multiplexing a single pair of electrodes: electrodes 1, 2, and 4 were used to detect electromyographic signals, and electrodes 3 and 4 were used to apply transcutaneous electrical stimulation. The multiplexing of electrode 4 was achieved through an optocoupler isolator. Electrode multiplexing effectively saved area.

[0036] (2) Design of electrical stimulation source for fabric-based signal conditioning circuit: A constant current source is used to output the stimulation current. The constant current source is powered by a single-stage boost circuit with BOOST topology, which converts the 3.7V lithium battery input voltage into a 40V output voltage. The amplitude of the stimulation current is controlled by the DAC (digital-to-analog converter) of the STM32L052 microcontroller. The direction of the stimulation current is controlled by the H-bridge at the load end of the constant current source, which consists of 4 optocouplers. Therefore, the duty cycle, frequency, and amplitude of the stimulation current can be adjusted in real time to ensure the output of electrically neutral current, thereby ensuring the comfort and safety of the treatment.

[0037] (3) Signal acquisition design of fabric-based signal conditioning circuit: The ADC (analog-to-digital converter) of STM32L052 is used to collect electromyographic signals and electrical stimulation waveforms, and the DMA (direct memory access) function of STM32L052 controls the sampling of ADC and subsequent data transmission to improve the real-time performance of the program. At the same time, the sampling rate is switched according to the different sampling signals: when collecting electrical stimulation waveforms, since the electrical stimulation waveforms are sparse short pulses (period 20ms, pulse duration ~3ms), the ADC in the electrical stimulation mode only performs high-speed sampling (40kHz) within 3ms after the pulse occurs, and does not sample at the rest of the time, thereby reducing the occupation of storage and transmission bandwidth; when collecting electromyographic signals, the ADC continuously performs low-speed sampling (720Hz) and synchronizes with signal transmission. In order to improve the signal-to-noise ratio of the electromyographic signal before sampling, an instrument amplifier and a bandpass filter are used to amplify the signal at the electrode end, the right leg drive circuit is used to suppress the common-mode noise from the human body, and the πRC network is used to filter out the power supply ripple noise caused by the electrical stimulation module and the Bluetooth module.

[0038] (4) Safety isolation design of fabric-based signal conditioning circuit: During the electrical stimulation process, in order to prevent the low-voltage EMG signal sampling electrode from connecting with the high-voltage electrical stimulation electrode on the skin surface, an optocoupler isolator is designed at the connection between the circuit and each electrode. In the electrical stimulation mode, the optocoupler of the EMG signal sampling electrode is blocked, and the optocoupler of the electrical stimulation electrode is switched in order; in the EMG signal sampling mode, the optocoupler of the electrical stimulation electrode is blocked, and the optocoupler of the EMG signal sampling electrode is normally open.

[0039] Specific:

[0040] Figure 1 The schematic diagram of the structure of the electrode array in this example is shown. Figure 1As shown on the left, electrode No. 1 121 and electrode No. 2 122 are the positive and negative input terminals of the electromyographic signal. Electrode No. 3 123 is the positive output terminal of the electrical stimulation, and electrode No. 4 124 is also used as the negative output terminal of the electrical stimulation and the output terminal of the right leg drive circuit. Among them, the electrical stimulation current output by electrodes No. 3 and 4 is too large, which is easy to produce polarization on the electrode surface, not only reducing the working efficiency of the electrode, but also causing a significant increase in impedance. In order to ensure the accuracy and stability of signal acquisition, the electromyographic signal sampling electrodes (electrodes No. 1 and 2) require lower impedance, so the electromyographic signal sampling electrodes (electrodes No. 1 and 2) and the output electrical stimulation electrodes (electrodes No. 3 and 4) need to be strictly separated. The right leg drive circuit has lower impedance requirements and is less affected by polarization, so electrode No. 4 can be used as the negative output terminal of the electrical stimulation and the output terminal of the right leg drive circuit at the same time. The four electrodes are compactly arranged on the fabric 11, and the reuse of electrode No. 4 124 effectively improves the space utilization. The shape of the above electrodes can be adjusted according to the needs of the scene. As shown in FIG. Figure 1 As shown in the cross-sectional view on the right, the interface between the electrode and the skin uses a conductive hydrogel to reduce the skin-electrode impedance. Medical double-sided tape is placed on the periphery of the hydrogel to ensure that the electrode can be stably attached to the skin surface during wearing. Although the use of Ag / AgCl with low polarization impedance as the electrode material can avoid the influence of electrode polarization and can realize the reuse of the electromyographic signal sampling electrode (electrodes 1 and 2) and the output electrical stimulation electrode (electrodes 3 and 4), in order to improve the versatility of the material and easily process the patterned electrode, which is beneficial to the layout of the circuit, the present invention selects metallized textiles and hydrogel as electrode materials.

[0041] Figure 2 The schematic diagram of the working mode of the electrode array is shown. Figure 6 It is a complete functional block diagram of the textile electronic system in this specific example; by configuring the optocoupler isolator and the H-bridge circuit, the electrodes are selectively connected to the peripheral circuit to achieve different working modes. Among them, the H-bridge is composed of 4 optocouplers. In the electromyography detection mode, the optocoupler inside the H-bridge on the right side of the figure is blocked, the 3 optocouplers on the left side of the figure are normally open, and electrodes 1, 2, and 4 are connected to the peripheral circuit. In the transcutaneous electrical stimulation mode, the 3 optocouplers on the left side of the figure are blocked, the optocouplers inside the H-bridge on the right side of the figure are switched in order, and electrodes 3 and 4 are connected to the peripheral circuit. Since the peripheral circuit on the left side of the figure is a low voltage of 3.3V or less, and the peripheral circuit on the right side of the figure is a high voltage of 40V or less, adding optocoupler isolation to the electrode can prevent the high and low voltages from short-circuiting on the skin surface, thus playing a protective role.

[0042] Figure 3The 3D exploded view of the entire textile electronic system is shown. From bottom to top, there are hydrogel 31, medical double-sided tape 32, bottom textile circuit and electrode array 33, textile base 34, top textile circuit 35, and patch electronic components 36. The medical double-sided tape 32 is cut into a specific shape by laser, and the hydrogel 31 is obtained by dripping a precursor solution into the groove formed by the medical double-sided tape 32 and curing it with ultraviolet light.

[0043] Figure 4 The actual picture of the textile electronic system and the wearing effect on the biceps brachii of the arm are shown. It can be seen that the electronic system has good bendability and high space utilization.

[0044] Figure 5 The program logic diagram of the textile electronic system in two modes, transcutaneous electrical stimulation and electromyography detection, is shown. Transcutaneous electrical stimulation is controlled by a timer interrupt with a period of 20ms, and it is determined at the end of the interrupt whether to proceed to the next cycle. The process first triggers DMA channel 1, so that the ADC samples the electrical stimulation to be applied (pulse duration ~3ms), and then immediately generates positive and negative electrical stimulation waveforms, while no sampling is performed in the remaining 17ms of the cycle, thereby reducing the occupation of storage space and transmission bandwidth. After DMA channel 1 completes a round of sampling, it immediately triggers DMA channel 2, and DMA channel 2 transmits the collected electrical stimulation waveform to the Bluetooth module, and finally transmits it to the host computer by Bluetooth. Electromyography detection is completed through the cyclic execution of DMA channel 1 and DMA channel 2. The process first triggers DMA channel 1, so that the ADC samples the electromyography signal. After the ADC conversion is completed, DMA channel 2 is immediately triggered, and the next round of electromyography signal sampling is performed at the same time. DMA channel 2 transmits the collected electromyography signal to the Bluetooth module, and finally transmits it to the host computer by Bluetooth. Among them, the use of DMA in two modes enables the fabric electronic system to collect and transmit signals simultaneously, greatly improving the efficiency and real-time performance of data transmission.

[0045] Figure 6 The functional block diagram of the textile electronic system is shown. In the electromyographic detection mode, the electromyographic signals detected by the three electrodes (electrodes 1, 2, and 4) are processed by the analog front end and bandpass filtering, and then collected by the 12-bit ADC channel of the microcontroller, and finally transmitted to the host computer via Bluetooth. In the transcutaneous electrical stimulation mode, the electrical stimulation current is output through the current source, where the current source is powered by a 3.7V lithium battery boosted to 40V, where the amplitude of the electrical stimulation current is controlled by the DAC of the microcontroller, and the direction of the electrical stimulation current is controlled by the H bridge. The electrical stimulation current detected by the three electrodes (electrodes 1, 2, and 4) is processed by the analog front end and bandpass filtering, and then collected at a high rate by the 12-bit ADC channel of the microcontroller within the electrical stimulation pulse time, and finally transmitted to the host computer via Bluetooth.

[0046] Figure 7 The electrical stimulation waveforms generated by the textile electronic system and the detected electromyographic signals are demonstrated. Figure 7 The electrical stimulation current pulse of a has the characteristics of bipolarity and electrical neutrality, which avoids the accumulation of charge on the skin and enhances the comfort and safety of applying transcutaneous electrical stimulation. The corresponding voltage is Figure 7 As shown in b. Figure 7 c is the electromyographic signal collected when the biceps brachii contracts. The signal-to-noise ratio is high, and the distribution of its power spectrum density is normal ( Figure 7 d).

[0047] Figure 8 The comparison between the fabric electronic system and a commercial PCB with the same function is shown. Figure 8 a is the current consumption of the two in idle mode (idle), when detecting electromyographic signals (EMG), and when applying electrical stimulation (EMC), respectively. Figure 8 b, Figure 8 c is the voltage waveform applied on the 1kΩ resistor of the textile electronic system and the commercial PCB board, respectively. The similar current consumption and almost identical EMS waveforms prove the reliability of the textile electronic system.

[0048] Fig. 9 The textile electronic system was worn on the biceps of a volunteer and loaded with a 5 kg weight for 2.5 minutes. Fig. 9 a is the electromyographic signal collected during the above loading process, Fig. 9 b. Fig. 9 c are the root mean square amplitude and short-time Fourier transform spectrum of the electromyographic signal. The increase in the root mean square amplitude of the electromyographic signal over time is caused by the enhanced neural recruitment caused by the gradual fatigue of the muscle. The frequency distribution of the short-time Fourier transform spectrum of the electromyographic signal shifts to low frequencies over time, which is caused by the decrease in the conduction velocity of the action potential caused by the gradual fatigue of the muscle. This proves the ability of the textile electronic system to detect muscle fatigue.

[0049] Fig.10 The ability of the textile electronic system to treat muscle fatigue was demonstrated by having volunteers perform Fig. 9 The corresponding weight-bearing experiment caused the muscles to accumulate fatigue, and then the electrical stimulation therapy function of the textile electronic system was turned on for 10 seconds. For comparison, two days later, the volunteer performed the weight-bearing experiment again and then rested for 10 seconds. The median frequency (MDF) of the electromyographic signal during the entire experiment is shown in Figure 1. Fig.10As shown in the figure, the lower the MDF value, the higher the degree of muscle fatigue. In 10 seconds of quiet rest, the MDF value only recovered 11%. In contrast, after 10 seconds of transcutaneous electrical stimulation, the MDF value recovered nearly 65%. This proves that the textile electronic system has the potential to accelerate the recovery of muscle bioelectric activity.

[0050] In order to further verify the ability of the textile electronic system to treat muscle fatigue, the maximum voluntary contraction force (MVC) of the muscle was used to quantify the degree of muscle fatigue: the lower the MVC value, the higher the degree of muscle fatigue. The MVC measurement method is as follows: the biceps brachii pulls the force sensor through a rope and a fixed pulley for 3 seconds, and the maximum reading of the force sensor is regarded as the MVC. Subsequently, a volunteer (the initial MVC of the biceps brachii is 170N) continuously pulls the force sensor through the above device. When the sensor reading is lower than 100N for 5 consecutive seconds, the biceps brachii is judged to be exhausted. After exhaustion, rest quietly or apply transcutaneous electrical stimulation therapy to relieve muscle fatigue, and the MVC value is measured once a minute. Fig.11 As shown, after applying transcutaneous electrical stimulation, MVC recovered to 98% of the initial state within 4 minutes, compared with the control group of calm rest, MVC only recovered to 89% of the initial state. This shows that the textile electronic system of the present invention can accelerate the recovery of muscle strength.

Claims

1. A fabric electronic system integrating muscle fatigue detection and treatment, characterized in that: Conductive fabric wires and physiological electrodes, vertical interconnection vias and patch components are integrated on the same fabric substrate. Conductive fabric wires are provided on both side surfaces of the fabric substrate and are interconnected with each other through vertical interconnection vias. The overall circuit includes an electrode array and a signal conditioning circuit. The electrode array is used to detect electromyographic signals and to apply transcutaneous electrical stimulation. The signal conditioning circuit is used for electromyographic signal amplification, electrical stimulation waveform conditioning and overall timing logic control, and has the functions of safety isolation and electrical stimulation waveform detection.

2. The muscle fatigue detection and treatment integrated textile electronic system according to claim 1, characterized in that: The electrode array is constructed by multiplexing a single pair of electrodes, and the electrode array includes electrodes 1 to 4, wherein electrode 1 and electrode 2 are the positive and negative input terminals of the electromyographic signal, electrode 3 is the positive output terminal of the electrical stimulation, and electrode 4 is simultaneously the negative output terminal of the electrical stimulation and the output terminal of the right leg driving circuit; wherein the electrode used for signal sampling is separated from the electrode used for applying electrical stimulation to avoid the signal sampling being affected by electrode polarization.

3. The muscle fatigue detection and treatment integrated textile electronic system according to claim 2, characterized in that: The signal conditioning circuit uses three independent optocouplers and an H-bridge circuit composed of four optocouplers, wherein electrode No. 1, electrode No. 2, and electrode No. 4 are connected to the peripheral circuit via an independent optocoupler respectively, and electrode No. 3 and electrode No. 4 are connected to the peripheral circuit via the H-bridge circuit. The four electrodes are selectively connected to the circuit by controlling the optocouplers to realize switching between electromyographic detection and electrical stimulation modes.

4. The muscle fatigue detection and treatment integrated textile electronic system according to claim 3, characterized in that: A constant current source is used in the signal conditioning circuit to output the stimulation current. The amplitude of the stimulation current is controlled by a digital-to-analog converter of a microcontroller. The direction of the stimulation current is controlled by an H-bridge circuit at the load end of the constant current source. The duty cycle, frequency and amplitude of the stimulation current are adjustable in real time to ensure the output of electrically neutral current.

5. The muscle fatigue detection and treatment integrated textile electronic system according to claim 3, characterized in that: In the electrical stimulation mode, the optocouplers connected to electrodes 1, 2, and 4 are blocked, and the optocouplers in the H-bridge circuit switch in order. In the electromyography detection mode, the optocouplers in the H-bridge circuit are blocked, and the optocouplers connected to electrodes 1, 2, and 4 are normally open.

6. The muscle fatigue detection and treatment integrated textile electronic system according to claim 1, characterized in that: The vertical interconnection vias are the locations on the fabric substrate where vias need to be formed to connect the circuits on both sides of the fabric. The conductive slurry is infiltrated into the texture structure of the fabric substrate at this location using air pressure injection, so that the corresponding areas of the fabric substrate are connected on the front and back sides.

7. The muscle fatigue detection and treatment integrated textile electronic system according to claim 1, characterized in that: The conductive fabric lines and physiological electrodes are formed by cutting the conductive fabric according to a pre-designed pattern using a laser, and then transferring the conductive fabric lines and physiological electrodes to both sides of the fabric substrate using a transfer method. The conductive fabric lines and physiological electrodes on both sides are connected through the vertical interconnection vias.

8. The muscle fatigue detection and treatment integrated textile electronic system according to claim 1, characterized in that: The chip components are soldered on the conductive fabric line using solder paste to form a complete circuit.

9. The muscle fatigue detection and treatment integrated textile electronic system according to claim 1, characterized in that: On the lower surface of the fabric base are conductive fabric lines and physiological electrode layers, as well as medical double-sided adhesive tape and hydrogel layers; the medical double-sided adhesive tape and hydrogel layer are formed by laser cutting of medical double-sided adhesive tape into grooves of the same shape as the physiological electrodes, and hydrogel precursor liquid is injected into the grooves and cured by ultraviolet light; on the upper surface of the fabric base are conductive fabric lines and patch electronic devices.

Images